Nanostructured formulations for the delivery of silibinin and other active ingredients for treating ocular diseases

ABSTRACT

Formulations are described, containing silibinin or other active ingredients incorporated in lipid nanoparticle systems of the SLN and NLC type, and based on calixarenes, possibly mucoadhesive, or in micellar and nanoparticle systems based on amphiphilic inulin copolymers for use in the treatment of neurodegenerative ocular diseases. The versatility of the calixarene compound is also described, capable of charging and releasing active ingredients characterized by low water solubility, easy chemical and enzymatic degradation, low bioavailability, either of natural origin or not, to be used in the treatment of ocular diseases.

FIELD OF THE INVENTION

The present invention relates to the field of products for the treatmentof ocular diseases and to formulations containing the same.

PRIOR ART

Uncontrolled neoangiogenesis is implicated in the etiology of variousdiseases such as: solid tumors, rheumatoid arthritis, psoriasis and, atthe ocular level, corneal neovascularization, age-related maculardegeneration (ARMD or AMD), macular edema, retinopathy of prematurity(ROP), choroidal neovascularization (CNV), diabetic retinopathy (DR) andneovascular glaucoma.

AMD, like many other chronic diseases related to ageing, has amultifactorial origin and its onset is caused by an unfavorablecombination of genetic and lifestyle-related factors.

Studies conducted on anti-VEGF (originally developed for cancer therapy)in the treatment of CNV led to use of pegaptanib (Macugen®, Pfizer) andranibizumab (Lucentis®, Genentech) in the treatment of CNV. Bevacizumab(Avastin®, Genentech) is also currently used “off label” in thetreatment of AMD.

It should also be considered that the treatment of AMD is not onlylimited to the treatment of choroidal neovascularization (intravitrealinjections of anti-VEGF and photodynamic therapy), but also includes theuse of a number of substances with antioxidant, anti-inflammatory andneuroprotective action capable of acting at different levels of theprocess leading up to the full-blown disease and acting to prevent theonset of the disease, slow its progression to advanced forms, reduce thetissue damage and enhance the action of anti-VEGF drugs.

Diabetic retinopathy (DR) is one of the most serious and frequentmicrovascular complications of type 1 and type 2 diabetes mellitus,which significantly affects the patient's quality of life as it oftenleads to blindness, due to the onset of macular edema and secondaryretinal vitreous neovascularization.

The therapies for DR currently available aim at contrasting theangiogenic and inflammatory processes of retinal diseases and as aresult, in some cases, they slow the progression of the disease.

Glaucoma is an optic neuropathy leading to the progressive loss of opticnerve tissue, leaving the head thereof exposed resulting in the loss ofvision. Uveitis is an inflammation of part or all of the tunica media(vascular) of the eye consisting of iris, ciliary body and choroid.

The therapeutic tools currently available for treating posterior uveitisare intravitreal injections or implants (Taylor S. R. Et al, Newdevelopments in corticosteroid therapy for uveitis, Ophthalmologica.2010; 224 Suppl 1:46-53), not without very important secondary effects(endophthalmitis, retinal edema, etc.) at the expense of the visualorgan.

Over the last two decades, intravitreal injections have been consideredvery valuable because, compared to other administration routes,typically allow reaching higher concentrations in the retina andvitreous. Nevertheless, the intravitreous route is associated to seriousrisks for the patient, such as retinal detachment, endophthalmitis andintravitreal hemorrhages. Moreover, this administration route requiresrepeated injections of the drug to ensure the therapeutic effect, whichoften is not well tolerated by the patient.

Therefore, the treatments currently available are unsatisfactory becauseof the existing disproportion in the benefits/side effects ratio.

For this reason, non-biodegradable controlled release systemsimplantable in the vitreous (Vitrasert®, Retisert®) have been developed,but even these have the same risks associated with intravitrealinjections, as well as the need for surgery for the implant and thepossibility of rejection.

A compromise between risks and benefits was obtained using theperiocular administration routes (peribulb, posterior juxtascleral,retrobulbar subtenon and subconjunctival), which are safer although lessefficient than the intravitreal.

These routes of administration exploit the use of traditional injectableformulations and allow the active ingredient to reach the target site(the vitreous and the retina) by diffusion through the scleral fibroustissue, which forms a barrier less resistant to drugs. The injected drugis in any case cleared through the front (outflow of the aqueous humor)or rear (retina and systemic circulation) path, requiring multipleadministrations associated with poor patient compliance (pain,cataracts, retinal detachment, endophthalmitis and vitreoushemorrhages).

Currently, therefore, the treatment of diseases of the posterior segmentof the eye has only drug delivery systems associated with undesiredeffects.

It is also known that the advanced drug delivery systems of thenanoparticle type today are the forefront of drug delivery.

Nanoparticle systems of a lipid nature such as solid lipid nanoparticles(SLN) and nanostructured lipid systems (NLC) are colloidal systemsconsisting of biocompatible lipids (pure triglycerides, complex mixturesof glycerides, waxes) and stabilized with non-toxic surfactants such aslecithins and poloxamers. They are between 100 and 500 nm in size. Atroom temperature, the particles are in the solid state.

It has already been shown that lipid nanoparticles increase thebioavailability of several drugs in the eye due to an increasedpre-ocular retention time compared to the conventional pharmaceuticalform, thus avoiding the repeated and frequent instillation (Int. J.Pharm., 238 241-245 (2002)).

Inulin is a natural polysaccharide extractable from various plants andfruits. It is a carbohydrate consisting of linear chains of D-fructoseunits bound through β-(2-1) gluco-furanoside bonds which occasionallybinds a glucose molecule at its reducing end. Inulin, due to the factthat it has many advantageous properties (absence of toxicity,biocompatibility, solubility in water and probiotic effect on intestinalbacterial flora), is used in countless applications (Kolida S, Gibson GR. J Nutr 2007; 137:2503S-2506S; Gocheva et al., Colloids and SurfacesA: Physicochem. Eng. Aspects 2011; 391:101-104), and among them many inthe biomedical field.

Recently, in order to get new drug delivery systems (DDS), such ashydrogels, nanoparticles, macromolecular bioconjugates and polymericmicelles, numerous researchers have focused their attention on thechemical modification of inulin.

This was chemically modified in the side-chain with primary amines,which have been used to obtain the conjugation with hydrophilic chains,such as polyethylene glycol (PEG), and with hydrophobic molecules suchas ceramide.

Calixarenes are cyclic polyphenols easy to synthesize, even at low cost,which are characterized by remarkable synthetic versatility, apredisposition toward their functionalization at different levels andfinally, a low degree of cytotoxicity and immunogenicity.

In recent years, calix[4]arenes have been intensely investigated as newmolecular platforms for biomedical applications, supported by lowcytotoxicity (Int. J. Pharm. 2004, 273, 57) and immunogenicity(Bioconjugate Chem. 1999, 10, 613) shown by their derivatives both invitro and in vivo.

The suitable functionalization of the calixarene backbone has providedderivatives with anti-inflammatory, antitumor, antimicrobial andvaccine-mimic activity (Curr. Drug Discov. Technol. 2009, 6, 306; Chem.Soc. Rev. 2013, 42, 366, US 2010/0056482; WO2005123660 A2).

Water-soluble calixarenes similar to cyclodextrins for the capacity ofcomplexing a drug within their hydrophobic cavity have been proposed asexcipients for the pharmaceutical industry, while amphiphiliccalixarenes capable of assembling in nanostructured systems in anaqueous medium are promising drug delivery systems (J. Sci. Ind. Res.2012, 71, 21; Chem. Soc. Rev. 2013, 42, 366, EP 1 293 248 A1; US2010/0185022 A19). Some of them have been properly engineered to releasethe drug according to external stimuli such as changes in theoxidation-reduction potential, temperature (ACSNANO, 2011, 5, 2880), pH(Phys. Rev. E, 2007, 73, 051904), enzymatic activity (RSC Advances,2013, 3, 8058), etc. The ability of calixarene derivatives to penetratethe cell membrane (Chem. Commun. 2012, 48, 1129; J. Am. Chem. Soc. 2008,130, 2892) and the ability to functionalize the calixarene backbone withhoming groups that recognize and bind to complementary receptors presenton the surface of the target cell, make calixarenes also promisingsystems for targeted drug delivery (Org. Biomol. Chem. 2015, 13, 3298).

Silibinin is a mixture of two diastereoisomers A and B in a proportionof about 1:1 contained in Silybum marianum.

Its main applications in the clinical field are: treatment of liverdiseases caused byalcohol, hepatic cirrhosis, Amanitapoisoning, viralhepatitis, and drug-induced liver diseases.

On the other hand, it is known that the bioavailability and efficacy ofsilibinin is rather limited due to its low solubility in water (430mg/L).

Silibinin seems to be an effective agent for the prevention andtreatment of malignant gliomas in humans (Rana P. Singh, Oncogene,2005).

Moreover, the antiangiogenic activity of silibinin particularly on AMDhas been shown in vitro and after oral administration of asilymarin-based preparation.

In light of the above, the prospect of having new pharmacologicalformulations that may facilitate the physician in the therapeutictreatment of eye diseases, in particular neurodegenerative diseases,such as macular degeneration and diabetic retinopathy, increases theinterest towards compounds such as silibinin functionalized to improvethe in situ availability thereof.

In addition to silibinin extensively studied with all the nanostructuredsystems described, other active ingredients of natural origin and notcharacterized by low water solubility, easy chemical and enzymaticdegradation, low bioavailability were investigated with some of thesenanostructured formulations, such as: sorafenib, curcumin, latanoprost.

Sorafenib (BAY43-9006, Bayer)

is a diaryl urea that acts on multiple targets (VEGF, PDGF, EGF; it isin fact defined as a multi-kinase inhibitor) with prevalent anti-VEGFaction, provided with proven anti-angiogenic action in tumors (EP1140840B1, Bayer), and it is the first antitumor agent approved inEurope for the treatment of hepatocellular carcinoma (Nexavar® tablets).

The therapeutic index of Sorafenib in the therapy of retinal diseasescan be increased by using the local administration, at the ocular level:in this way, the pharmacological effect can be obtained while limitingthe occurrence of systemic side effects. Moreover, the localadministration allows the use of limited doses compared to thoserequired for having the same effect via systemic administration and thusa reduction in the costs of the finished product.

Curcumin

is a yellow polyphenol (diferuloylmethane) extracted from the rhizome ofCurcuma Longa, an Asian plant used both in the culinary industry and inmedicine for its curative properties in biliary diseases and in someinflammatory conditions.

Latanoprost

is an active ingredient which like bimatoprost and travoprost is part ofthe prostaglandin analogs. Prostaglandin analogs are a class of drugsfor topical use that has recently been used in the treatment ofopen-angle glaucoma; initially, they were not recommended as first-linetreatment due to the lack of information about their long-term effects.Among the side effects associated with long-term treatment withprostaglandins, the major ones concern changes in the iris pigmentation,thickening and lengthening of eyelashes, onset of macular edema(Alexander C L et al., Prostaglandin analog treatment of glaucoma andocular hypertension; Ann Pharmacother., 2002).

BRIEF DESCRIPTION OF THE FIGURES

FIG. 1 shows the percentage of silibinin released by SLN-A in PBS at pH7.4 as a function of the incubation time, compared to the dissolutioncurve of free silibinin.

FIG. 2 shows the percentage of silibinin released by NLC-B systemscoated with INU-DETA and chitosan in PBS at pH 7.4 as a function of theincubation time, and dissolution curve of free silibinin.

FIG. 3 shows the percentage of silibinin released by the polymericmicelles of INU-C8 and INU-C8-PEG in PBS at pH 7.4 as a function of theincubation time, compared to the diffusion curve of free silibinin.

FIG. 4 (a and b) shows the cytocompatibility profile of empty micellesof INU-C8 and INU-C8-PEG on the 16HBE cell line after 4 hours (4 a) and24 hours (4 b) incubation at different concentrations.

FIG. 5 A shows the effect on ARPE-19 cells pretreated for 20 hours withthe INUC8PEG-Sorafenib system, with the empty carrier INUC8PEG and withSorafenib tosylate, thereafter, they were exposed to insult with H₂O₂;quantification of LDH release into the medium.

FIG. 5 B shows the effect on ARPE-19 cellsinsulted with H₂O₂ for threehours and post-treated for 20 hours with the INUC8PEG-Sorafenib system(C8PEGSor), with the empty carrier INUC8PEG (C8PEG) and with Sorafenibtosylate (Sor); quantification of LDH release into the medium.

FIG. 6 A shows the effect on ARPE-19 retinal cells pretreated for 20hours with the INUC8PEG-Sorafenib system, with the empty carrierINUC8PEG and with silibinin, then exposed to insult with H₂O₂;quantification of LDH release into the medium.

FIG. 6 B shows the effect on ARPE-19 retinal cells insulted with H₂O₂for three hours and post-treated for 20 hours with theINUC8PEG-silibinin system (C8PEGSlb), with the empty carrier INUC8PEG(C8PEG) and with silibinin (Slb); quantification of LDH release into themedium.

FIG. 7 shows the representative Western blotting performed on sampleswithout (control, C) or with H₂O₂ (H), and treated or not with INUC8PEG(1 μM and 10 μM), with lNUC8PEGSlb (1 μM and 10 μM) or with Slb (1μM and10 μM) Anti-PARP1 1:800 primary antibodies were used (Cell Signaling).The densitometric analysis of the bands (histograms) was normalized forβ-actin.

FIG. 8 shows the percentage of silibinin released by the calixarenenanoparticles in PBS at pH 7.4 as a function of the incubation time.

FIG. 9A shows the effect on ARPE-19 retinal cells pretreated for 20hours with the Calixarene-Silibiiin system (CalixSlb), with the emptycarrier (calix) and with silibinin alone, and thereafter exposed to 50μM FeSO₄; quantification of LDH release into the medium.

FIG. 9B shows the effect on ARPE-19 retinal cells treated with FeSo₄ 50μM for 5 hours and post-treated for 20 hours with theCalixarene-Silibinin system (CalixSlb), with the empty carrier (calix)and with silibinin (Slb) alone; quantification of LDH release into themedium.

FIG. 10A/B shows the representative Western blotting performed onsamples without (CTR) or with FeSO4 (Fe) and treated or not with Calix(1μM), with CalixSlb(1 μM) or with Slb (1 μM). Anti-VEGF 1:100 primaryantibodies were used (Santa Cruz) (10 A) and the representative Westernblotting performed on samples without (CTR) or with FeSO4 (Fe) andtreated or not with Calix(0.1 μM and 1 μM), with CalixSlb (0.1 μM and 1μM) or with Slb (0.1 μM and 1 μM). Anti-cathepsin D 1:200 primaryantibodies were used (Santa Cruz). The densitometric analysis of thebands (histograms) was normalized for β-actin (10B).

FIG. 11 shows the protective effect of the calixarene system towards theactive ingredient curcumin, for which a degradation of 90% in 30 min in0.1 M PBS and in serum-free medium is shown for comparison,

FIG. 12 shows the results of the cytotoxicity tests on SIRC cornealcells following treatment with curcumin, calixarene system andcalixarene-curcumin system.

FIG. 13 shows the results of the cytotoxicity tests MIT assay on J744macrophages of curcumin, calixarene and calixarene-curcumin.

FIG. 14 shows the vitality of J744 macrophages stimulated with LPS andpre-exposed to treatment with curcumin, calixarene system andcalixarene-curcumin system.

FIG. 15 shows the reduction in the degradation of the constituentprotein IκBα in J744 macrophages subjected to stress from LPS in thepresence of curcumin, with curcumin, calixarene system andcalixarene-curcumin system.

FIG. 16 shows the reduction of NFκB in J744 macrophages subjected tostress from LPS in the presence of curcumin, calixarene 1 andcalixarene-curcumin.

FIG. 17 shows the expression of iNOs and COX2 in J744 macrophagessubjected to stress from LPS and their reduction in the presence oftreatment with curcumin, calixarene 1 and calixarene-curcumin.

FIG. 18A/B shows the results of the histological score and of theprotein assay in aqueous humor of animals treated with silibininincorporated or not in the calixarene system, with curcumin incorporatedor not in the calixarene system in a model of uveitis.

FIG. 19 A/B shows the trends of the reduction in the intraocularpressure in a model of hypertonia after single administration (A) andafter chronic treatment of the calixarene-latanoprost system and of thecommercial product IOPIZE containing latanoprost.

SUMMARY OF THE INVENTION

Formulations for topical administration are described, containingsilibinin incorporated in SLN and NLC lipid nanoparticle systems, andbased on calixarenes, possibly mucoadhesive, or in micellar andnanoparticle systems based on amphiphilic inulin copolymers for use inthe treatment of neurodegenerative ocular diseases.

DETAILED DESCRIPTION OF THE INVENTION

The present invention overcomes the drawbacks described above withformulations for topical application containing silibinin incorporatedin:

(1) lipid nanoparticle systems of the SLN (Solid Lipid Nanoparticles)and NLC (Nanostructured Lipid Carriers) type;

(2) calixarene-based nanostructured systems;

(3) micellar and nanoparticle systems based on amphiphilic inulincopolymers, examples of incorporation and release of other activeingredients that have a use rationale for the ocular diseases ofinterest are provided for the latter.

Said formulations are capable of delivering the active ingredient up tothe vitreous or to the retina in therapeutically effective doses for thetreatment of neurodegenerative ocular diseases such as maculardegeneration, diabetic retinopathy, glaucoma. The present inventionfurther relates to the processes of preparation of the nanoparticlesystems incorporating silibinin as defined above.

In particular, a general procedure described hereinafter was folio edfor the preparation of SLN and NLC type systems.

The lipid phase (consisting of a solid lipid or a mixture of a liquidlipid with a solid one) is molten to about 5-10° C. above its meltingpoint. Silibinin is solubilized in an aliquot of ethanol and then addedto the molten lipid mixture under magnetic stirring.

The hot lipid mixture containing silibinin is then precipitated in anaqueous solution containing water, a surfactant or a mixture ofsurfactants (precipitation method), or emulsified with an aqueoussolution containing water, a surfactant or a mixture of surfactants,previously heated at the same temperature. In the latter case, theresulting pre-emulsion is either: dispersed in water or an aqueousmedium cooled at a temperature of between 2 and 5° C. (microemulsionmethod), or subjected to high pressure homogenization (high pressure hothomogenization method). In all cases, the resulting nano-emulsion isallowed to cool to room temperature to then be purified throughexhaustive dialysis (COMW 12000-14000) against distilled water.

Thereafter, the cryoprotectant is added to the nanoparticle dispersion,which can be subjected to centrifugation (4000 rpm for 10 min at 10°C.). Finally, after freeze-drying, the solid lipid nanoparticles areretrieved and stored in freezer for later characterization and/or coatedwith the mucoadhesive polymers. In the latter case, the INU-EDA andINU-DETA polymers and chitosan, in 0.1% aqueous solution, are added tothe nanoparticle suspensions and incubated for 30 min at roomtemperature and under magnetic stirring.

The above lipid phase consists of lipids, for example selected from:triglycerides, such as tristearin, tripalmitin, caprylic/capric acidtriglycerides (Mygliol); diglycerides such as Precirol ATO 5 (glyceryldistearate); monoglycerides such as glyceryl monosterate; aliphaticalcohols, such as cetyl alcohol; fatty acids (C10-C22); fatty acidesters with fatty alcohols, such as cetyl palmitate; mixtures of mono-,di- and triglycerides of pegylated and non-hehenic acid such asCompritol HD-5-ATO (PEG-8 behenate and tribehenin) and Compritol 888ATO(mixture of mono-, di- and tribehenate); mono-, di- and triglycerides ofpegylated caprylic and caproic acid such as Accocon CC-6.

The substances used as surfactants/co-surfactants in the process can befor example selected from: non-ionic surfactants including lecithinssuch as Epikuron 200; polyethylene glycol and polypropylene glycol blockcopolymers such as Pluronic; pegylated sorbitan derivatives, such asTween; fatty alcohol ethers with polyethylene glycol such as Brij; ionicsurfactants including bile salts such as sodium taurocholate; quaternaryamines including cetylpyridinium chloride and bromide dioctadecyldimethyl ammonum.

The substances used as cryoprotectants in the process can for example beselected from: sugars such as lactose and trehalose; polymers such aspolyvinylpyrrolidone (PVP).

The substances used to impart mucoadhesion in the process are forexample selected from: inulin polymers bearing amine groups (INU-EDA andINU-DETA), low molecular weight polymers (Chitosan) and cationicsurfactants (CCP and DDAB).

According to a further embodiment, the invention relates to formulationsfor ophthalmic use containing inulin-based copolymers of the followingformula (I) or (II),

wherein R is —(CH₂)—CH₃; where p is in the range between 0 and 19;

wherein R is —(CH₂)_(p)—CH₃; where p is in the range between 0 and 19and n is in the range between 9 and 450and to such copolymers.

The inulin-based copolymers of formula (I) and (II) as given above areobtained by functionalization of inulin with aliphatic chains C8 or withchains of C8 and PEG.

These copolymers, which have amphiphilic features, have proven to beable to aggregate to form micelles or nanoparticles, to incorporateflexible and different amounts of drug and release it into the activeform for a prolonged and controlled time, moreover, they are highlybiocompatible and allow easy making of the ophthalmic formulation.

The formulation is obtained by adding a certain amount of activeingredient such as sorafenib or silibinin to a polymer solution in DMF.The resulting solution is then dried under vacuum and dispersed in PBSat pH 7.4 by ultrasonication and stirring cycles (3 cycles of 10minutes). Thereafter, the dispersion is placed in an orbital shaker for18 hours at 25° C. and then dialyzed against water with a membranehaving nominal cut-off (MW00) of 1000 Da.

Finally, the resulting dispersion is freeze-dried.

According to a further embodiment of the present invention, it refers toformulations for ophthalmic use containing nanostructured systems basedon amphiphilic calixarenes.

In such systems, the presence of multiple positively charged ligandunits, in addition to imparting mucoadhesive properties, can facilitatethe crossing of the corneal and retinal epithelium by the molecularrecognition of complementary receptors present on the cell surface.

In particular, the present invention relates to formulations for topicalophthalmic use comprising cationic macromolecules consisting ofcalix[4]arene derivatives functionalized with alkoxyamines, includingcholine, to obtain new carriers of general formula (A)

wherein:

R═CH3, (CH₂)_(x)CH₃, (CH₂)xOH

R₁═CH3, (CH₂)_(x)CH₃, (CH₂)xOH

Wherein

x=1-3

n=4, 6, 8

m=2-15

and wherein when R═R₁═CH₃ m is different from 2-9which, in addition to delivering known active ingredients, are alsoprovided with their own bioactivity which may potentiate that of theactive ingredient.

As can he seen, formula A represents calixarene derivatives that differin the number of phenolic units forming the macrocycle (n=4, 6, 8), inthe length of the hydrophobic tails (m=2-15, indicates the number of CH2groups), in the structure of the polar group present at the upper rim ofcalixarene (R and R1=CH3, (CH2)xCH3, (CH2)xOH, where x=1-3 andcombinations thereof).

The calixarene compounds as described above are new and they are also anobject of the present invention; these compounds have shown greatversatility in charging and releasing active ingredients characterizedby low water solubility, easy chemical and enzymatic degradation, lowbioavailability, either of natural origin or not, to be used in thetreatment of ocular diseases.

Choline as targeting molecule guides and promotes the crossing of thecorneal epithelium, of the blood-retinal barrier and of the retinalepithelium (Adv. Drug Deliv. Rev. 2006, 58, 1136) where choline carriersare present.

Also in this case, as for the inulin-based copolymers described above,it was found that the calixarene systems have shown the ability to formnanoaggregates capable of incorporating and releasing silibinin or otheractive ingredients such as: curcumin/latanoprost.

Biocompatibility and ease of preparation characterize the formulationwhich is obtained by simple dissolution of the calixarene derivative inPBS (pH 7.4), addition of an excess of active ingredient (phasesolubility method), sonication for 15 minutes, stirring at 25° C. for2-3 days, centrifugation and filtration on GHP 0.2 μm filter.

The nanoparticle systems obtained in the present invention have anaverage diameter in the range between 50 and 200 nm with apolydispersity index below 0.5.

A pharmacologically effective amount of active ingredient isincorporated in the described nanoparticles. In particular, thenanoparticle systems obtained in the present invention have a DrugLoading in the range between 1 and 15% w/w.

Further features and advantages of the present invention will appearmore clearly from the following description of some embodiments thereof,made by way of non-limiting example.

The formulations according to the present invention containing an activeingredient selected from: silibinin or sorafenib or curcumin orlatanoprost in lipid nanoparticle systems of the SLN (Solid LipidNanoparticles) and NLC (Nanostructured Lipid Carriers) type, or innanostructured systems based on calixarenes, either mucoadhesive or not,or in micellar and nanoparticle systems based on amphiphilic inulincopolymers, allow the topical administration of the active ingredientsfor the treatment of neurodegenerative ocular diseases such as: CNV,AMD, macular edema, neovascular glaucoma, macular edema, retinopathy ofprematurity (ROP), diabetic retinopathy (DR), uveitis, endophthalmitis,retinitis, choroiditis, chorioretinitis, retinal complications ofsystemic diseases.

The formulations are normally in the form of freeze-dried solid productand may contain, in addition to the active ingredient incorporated inthe lipid, polymer or calixarene nanostructure as described above, alsocomponents such as surfactants and/or cryoprotectants and otherexcipients commonly used in ophthalmic preparations.

Example 1 Preparation of SLN Containing Silibinin (SLN-A)

The procedure and the experimental data obtained with the SLN object ofthe invention prepared with Compritol HD-5-ATO, loaded with silibinin,are described hereinafter.

Preparation of SLN-A

The SLN -A were prepared with the high pressure hot homogenizationmethod. Two hundred milligrams of Compritol HD5ATO were molten to about5-10° C. above its melting point (65-70° C.). The drug (68 mg) wassolubilized in an aliquot of ethanol (0.5 mL) and then added to themolten lipid mixture under magnetic stirring. The hot lipid mixturecontaining the drug was then emulsified in an aqueous solution of thePluronic F68 surfactant (60 mg in 100 mL), previously heated at the sametemperature. The resulting pre-emulsion is subjected to high pressurehomogenization (4 cycles at 7500±2500 psi) using the Emulsiflex-C5equipment (Avestin), placed in a hot water bath at a temperature of65-70° C. The resulting nano-emulsion is allowed to cool to roomtemperature to then be purified by dialysis (COMW 12000-14000) againstdistilled water. Thereafter, the cryoprotectant trehalose(lipids:cryoprotectant weight ratio=1:1 w/w) is added to thenanoparticle dispersion, which was subjected to centrifugation (4000 rpmfor 10 min at 10° C.).

Finally, after freeze-drying using a Modulyo freeze-dryer, the SLN areretrieved and stored in freezer for subsequent characterization.

Size Determination and Zeta Potential Measurement of SLN-A Zystems

The average diameter and the polydispersity index (PDI) of the SLN-Asystems prepared were determined by photo-correlation spectroscopy (PCS)using a Zetasizer Nano ZSP (Malvern Instrument). Each sample wassuitably diluted for the analysis with an aqueous solution of NaCl 0.9%w/w, filtered through 0.2-μm filters and the reading was made at anangle of 173° relative to the incident ray and analyzed in triplicate.

The zeta potential was measured according to the principles of the laserdoppler velocimetry and of the light scattering analysis (M3-PALStechnique) using a Zetasizer Nano ZSP (Malvern) with a He—Ne laser,power=4.0 mW, wavelength=633 nm.

The results obtained for average diameter, PDI and zeta potential aregiven in Table

TABLE 1 Average hydrodynamic diameter, polydispersity index (PDI), zetapotential of SLN-A systems. Table 1 DLS (in NaCl 0.9% w/w) Z-averagePotential ζ (nm) PDI (mV ± SD) PRE-freeze drying 189.0 0.22 −9.4 ± 1.2POST-freeze drying 171.5 0.31 −6.5 ± 3.5

Determination of Drug Loading (% DL) of SLN-A

In order to determine the amount of silibinin loaded in the SLN-Asample, 10 mg of the composition previously subjected to freeze-dryingwere solubilized in tetrahydrofuran (THF). The organic solution was thentreated with methanol to precipitate lipids and extract the activeingredient. The resulting suspension was then filtered through 0.45 μmfilters and analyzed by HPLC. The results obtained in terms of % DL(expressed as a percentage of the active ingredient loaded into the SLN,considering 100 mg of the material subjected to freeze-drying,consisting of lipids+active ingredient) was found to be 8.5% w/w.

Releases at pH 7.4 of Silibinin from SLN-A

The system described in the present invention was subjected to releasestudies in vitro at 37° C. using a phosphate buffer at pH 7.4 withincubation times in the range between 0 and 12 hours. The resultsobtained have shown that the system of the present invention slowlyreleases the drug up to a maximum of 7.8% w/w within 12 hours. Therelease and dissolution profiles of the drug after incubation at pH 7.4and at 37° C. are shown in FIG. 1.

The system described is stable, i.e. it releases the drug very slowlyinto the external medium at pH 7.4 and this can be advantageous in orderto optimize the delivery of the active ingredient in the pathologicalsite by the nanoparticle containing it.

Example 2 Preparation of NLC Containing Silibinin (NLC-B)

By way of non-limiting example, the procedure and the experimental dataobtained with the NLC object of the invention prepared with CompritolHD-5-ATO, Gelucire 44/14 and Acconon CC-6, loaded with silibinin, aredescribed hereinafter.

Preparation of NLC-B

The NLC-B were prepared with the solvent precipiation-evaporationmethod.

Compritol HD5ATO (250 mg) was molten to about 5-10° C. above its meltingpoint (65-70° C.) and the drug (30 mg) was added to the molten lipid.Gelucire 44/14 (100 mg) and Acconon CC-6 (100 mg) were solubilized inethanol (2.0 mL) and then added to the molten lipid mixture undermagnetic stirring. The hot lipid mixture containing the drug and thesurfactants was then precipitated in a hot aqueous solution containingsurfactant sodium taurocholate (100 mg in 100 mL), previously heated atthe same temperature and subjected to homogenization using Ultra-Turrax(13.500 rpm). The hot nanoparticle suspension, still under stirring, isplaced in an ice bath until its temperature reaches the value of 10° C.The resulting nanoparticles are then purified by dialysis (COMW12000-14000) against distilled water for 3 days and then thecryoprotectant trehalose is added (lipid:cryoprotectant weight ratio=1:2w/w). Finally, after freeze-drying using a Modulyo freeze-dryer, the NLCare retrieved and stored in freezer for subsequent coating with aninulin derivative (INU-DETA) and chitosan. In the case of coating withINU-DETA, 9 mL of dyalized nanoparticle suspension (conc. of 4.3 mg/mL)were incubated with 1 mL of 0.1% INU-DETA for 1 h under magneticstirring. In the case of coating with low molecular weight (5000 Mw)chitosan, 9 mL of dyalized and freeze-dried nanoparticles (conc. of0.165 mg/mL) with addition of trehalose were incubated with 1 mL of 0.1%Chitosan for 30 min under magnetic stirring. The coated nanoparticleswere then freeze-dried and stored as a powder for subsequentcharacterization.

Size Determination and Zeta Potential Measurement of NLC-B Systems

The average diameter and the polydispersity index (PDI) of the NLC-Bsystems coated with INU-EDA and chitosan prepared were determined byphoto-correlation spectroscopy (PCS) using a Zetasizer Nano ZSP (MalvernInstrument). Each sample was suitably diluted for the analysis with anaqueous solution of NaCl 0.9% w/w, filtered through 0.2-μm filters andthe reading was made at an angle of 173° relative to the incident rayand analyzed in triplicate.

The zeta potential was measured according to the principles of the laserdoppler velocimetry and of the light scattering analysis (M3-PALStechnique) using a Zetasizer Nano ZSP (Malvern) with a He—Ne laser,power=4.0 mW, wavelength=633 nm.

The results obtained for average diameter, PDI and zeta potential aregiven in Table 2.

TABLE 2 Average hydrodynamic diameter, polyclispersity index (PDI), zetapotential of NLC-B coated with INU-DETA and chitosan. DLS (in NaCl 0.9%)Z-average Potential ζ (nm) PDI (mV ± SD) NLC-B INU-DETA 236.8 0.45 −1.1NLC-B chitosan 69.1 0.45 +18.2

Determination of the % DL of the NLC-B Coated with INU-DETA and Chitosan

In order to determine the amount of silibinin loaded in the NLC-Bsamples coated with INU-DETA and chitosan, 2 mg of the compositionspreviously subjected to freeze-drying were hot-solubilized in 8 mL ofethanol (EtOH) and sonicated for 3 min.

The resulting solutions were then filtered with 5.00 μm regeneratedcellulose filters and analyzed with HPLC.

The results obtained in terms of % DL (expressed as a percentage ofactive ingredient loaded into the NLC, considering 100 mg of thematerial subjected to freeze-drying, consisting of lipids+activeingredient) were found to be 6.05% w/w for the NLC-B coated withINU-DETA and 3.07% w/w for the NLC-B coated with chitosan.

Releases at pH 7.4 of the Active Ingredients from NLC-B coated withINU-DETA and Chitosan

The NLCB systems coated with INU-DETA and chitosan described in thepresent invention were subjected to release studies in vitro at 37° C.using a phosphate buffer at pH 7.4 with incubation times in the rangebetween 0 and 12 hours. The results obtained have shown that bothsystems of the present invention slowly release the drug up to a maximumof 50% w/w within 12 hours for the NLC-B coated with INU-DETA and up toa maximum of 30% w/w within 12 hours for the NLC-B coated with chitosan.The release and dissolution profiles of the drug silibinin from the 2coated systems after incubation at pH 7.4 and at 37° C. are shown inFIG. 2.

Preparation of Polymeric Micelles Based on INU-C₈and INU-C₈-PEG₂₀₀₀

By way of non-limiting example, the procedure and the experimental dataobtained with polymeric micelles object of the invention based on INU-C₈and INU-C₈-PEG₂₀₀₀, loaded with silibinin or sorafenib, are describedhereinafter.

Determination of the Critical Aggregation Concentration (CAC) of INU-C₈and INU-C₈ PEG₂₀₀₀ Copolymers

The production of INU-C₈ and INU-C₈-PEG₂₀₀₀ copolymers was carried out,with a good yield, following procedures already existing in theliterature.

The CAC of INU-C₈ and INU-C₈-PEG₂₀₀₀ copolymers was determined byspectrofluorimetric analysis, using pyrene as fluorescent probe. 20 μLof a solution of pyrene in acetone (6.0×10⁻⁵M) were placed into vialsand evaporated at 37° C. on an orbital shaker until dryness. Thereafter,2 mL of an aqueous solution of copolymer at increasing concentration andin the range between 1×10⁻⁵ and 5 mg/mL were added into the vialscontaining the pyrene residue so as to obtain a final concentration ofpyrene equal to 6.0×10⁻⁷ M. The dispersion thus obtained were maintainedat 37° C. for 24 hours under constant stirring in order to balance theprobe with the micelles. The emission and excitation spectra of pyrenewere recorded using the following wavelengths, respectively: 373 nm and333 nm. The results are shown in Table 3.

Preparation of Polymeric Micelles of INU-C8 and INU-C8-PEG Loaded withSilibinin or Sorafenib

The polymeric micelles loaded with silibinin and sorafenib were preparedthrough the dry complexation method (kneading). In detail, 200 mg ofINU-C8 or INU-C8-PEG were dry mixed with the drug (50 mg) using a mortarand pestle and ground in the presence of ethanol (5 mL). Thereafter, thedry matrix formed by the polymer wherein the drug was dispersed evenly,obtained after evaporation of ethanol, was hydrated slowly and undermechanical stirring in order to promote the self-aggregation of unimersand the incorporation of the drug within the hydrophobic core of theresulting micelles.

The resulting dispersion was subjected to sonication and stirring cycles(3 cycles of 10 minutes). Thereafter, the dispersion was centrifuged at2000 rpm for 5 minutes and filtered on syringe filters with 5 μm cut offto remove the drug not incorporated.

Finally, the resulting dispersion was frozen in liquid nitrogen andfreeze-dried.

Determination of the % DL of the polymeric micelles of INU-C8 andINU-C8-PEG₂₀₀₀ 3 mg of micelles loaded with silibinin or loaded withsorafenib were dispersed in methanol (5 mL); the dispersion wassonicated for 10 minutes and then left to stir vigorously for 4 hours.After this time, the dispersion was filtered using a syringe filter with0.2 μm cut off, and finally the filters were washed with methanol (5 mL)to obtain a final volume of 10 mL. For the determination of silibinin at600 μL of the solution in methanol obtained from the extractionprocedure, 400 μL of 1% acetic acid (v/v) were added to comply with thecomposition of the eluent mixture used for the HPLC analysis. Therefore,the amount of drug extracted from the micelles was determined throughHPLC analysis, using a C6-phenyl, methanol:acetic acid column at 1%(v/v) (60:40) as eluent phase. The flow rate was set to 0.65 mL/min andthe eluate was monitored at 288 nm.

For the determination of sorafenib, 1 mL of the solution in methanolobtained from the extraction procedure was directly analyzed by HPLC inorder to determine the amount of drug incorporated by the micelles. TheHPLC analysis was performed using a C6-phenylmethanol:water (v/v)(90:10) column as eluent phase. The flow rate was set to 1 mL/min andthe eluate was monitored at 266 nm.

The results are shown in Table 4. Determination of the average size andof the zeta potential of polymeric micelles of INU-C8 and INU-C8-PEG

The size distribution of micelles was determined through dynamic lightscattering measurements using the Malvern Zetasizer Nano ZS. Thesemeasurements were conducted at a fixed angle of 173° and at atemperature of 25 ° C. The aqueous solutions of micelles (2 mg/mL) wereanalyzed after filtration through cellulose membrane filters with 5 μmcut off. The average hydrodynamic diameter and the polydispersity index(PDI) were obtained using cumulative analyses of the correlationfunction. The zeta potential (mV) was calculated by the electrophoreticmobility and using the Smoluchowsky relation, assuming that K·a>>1(where K and a are the Debye-Hückel parameter and the particle radius,respectively). The results are shown in Table 4. As can be seen, all thecopolymers are able to incorporate the hydrophobic drug sorafenib andsilibinin.

Release Studies

In order to assess the ability of the systems obtained to release theincorporated drug, appropriate amounts of polymeric micelles of INU-C8and INU-C8-PEG (15 mg) were dispersed in PBS, pH 7.4 (5 mL) andtransferred in a floating dialysis membrane Spectra/Por with nominal cutoff (MWCO) of 1 kDa. The dialysis membranes containing the micelledispersions loaded with drug and the drug alone were immersed in PBS atpH 7.4 (50 mL) and incubated at 37° C. for 24 hours under continuousstirring (100 rpm) in a Benchtop 8080 Orbital Shaker incubator model420. At scheduled time intervals, aliquots of external medium (1 mL)were taken from outside the dialysis membrane and replaced with an equalamount of fresh medium.

The samples taken were freeze-dried, suspended in methanol:acetic add 1%(v/v) and analyzed by HPLC in order to determine the amount of drugreleased. By way of example, the release graph of the active ingredientsilibinin incoporated in the systems is shown. All the release all dataobtained were compared with the diffusion profile of silibinin alone(0.25 mg), obtained using the same procedure (FIG. 3).

The data were corrected taking into account the dilution process. Eachexperiment was conducted in triplicate and the results were found to bein conformity with the standard error ±5%. As can be seen from thegraph, the polymeric micelles of INU-C8 and INU-C8-PEG loaded withsilibinin show a very slow release kinetics compared to the diffusion offree silibinin (less than 5% w/w of silibinin is released after 12 hincubation). Similar release profiles were also obtained for the activeingredient sorafenib.

Stability Studies

The stability of micelles of INU-C8 and INU-C8-PEG loaded with silibininor sorafenib was assessed by incubating the freshly freeze-dried systemsfor 1, 2 and 3 months at 4° C. and 25° C. In particular, the samplesfreshly prepared and freeze-dried were stored at a controlledtemperature for 1, 2 and 3 months. After the incubation period, thesamples were dispersed in bidistilled water (2 mg/mL) and analyzed bydynamic light scattering measurements in order to evaluate the averagediameter, polydispersity index and zeta potential thereof. Separately, 3mg of sample were dispersed in methanol (5 mL); the dispersion was firstsonicated for 10 minutes and stirred for 2 h and finally, filteredthrough syringe filters with 5 μm cut off and diluted with additional 5mL methanol. The amount of active ingredient extracted was determinedthrough HPLC analysis, using the same procedure described for thedetermination of drug loading.

The results obtained show that both the micelles prepared and the drugloaded have good physical stability for long periods of storage. As anexample, Table 5 shows the stability data related to NU-C8 micellesloaded with silibinin or sorafenib obtained through dynamic lightscattering measurements in order to evaluate changes in the averagediameter, in the PDI and in the zeta potential, and HPLC analysis toassess the drug loading and stability of the loaded drug.

TABLE 5 Stability of INU-C8 micelles loaded with silibinin/sorafenib, 1and 2 after 3 months of storage at 4 and 25° C. Average Zeta DrugIncubation diameter potential loading time (nm) PDI (mV) (%) INU-C₈micelles Time 0 164.9 0.27  +21.9 ± 3.82 1.7 ± 0.5 1 month 4° C. 153.30.37 +10.9 ± 4.3 1.9 ± 0.9 1 month 25° C. 188.2 0.26 +10.9 ± 4.2 1.7 ±0.9 2 month 4° C. 195.8 0.39 +7.38 ± 3.4 1.7 ± 0.3 2 month 25° C. 185.60.44 +6.37 ± 3.9 1.7 ± 0.7 3 month 4° C. 137.8 0.32 +8.76 ± 4.5 1.7 ±0.3 3 month 25° C. 151.6 0.38 +7.88 ± 3.3 1.7 ± 0.7 INU-C₈ Sorfenibmicelles Time 0 150.4 0.16 +19.9 ± 4   18.4 ± 0.5  1 month 4° C. 153.80.15 +23.82 ± 4.72  19 ± 0.9 1 month 25° C. 198.5 0.098  +29.9 ± 5.39 17 ± 0.9 2 month 4° C. 160.8 0.15  +31.6 ± 5.46 17.5 ± 0.3  2 month 25°C. 431.8 0.29 −0.644 ± 3.33 18.3 ± 0.7  3 month 4° C. 250.3 0.22 +15.7 ±5.5 18.1 ± 0.3  3 month 25° C. 318 0.273 +17.1 ± 3.4 17.3 ± 0.7 

In vitro Cytocompatibility Studies

The biocompatibility of empty micelles of INU-C8 and INU-C8-PEG wasevaluated on the human bronchial epithelium (16HBE) cell line throughMTS assay, using a commercial kit (Cell Titer 96 Aqueous One SolutionCell Proliferation assay, Promega). The cells were plated on 96 wellplates with a density of 2·10⁴ cells per well, and suspended inDulbecco's modified eagle's medium (DMEM), enriched with 10% vol/vol offetal bovine serum (FBS), 1% vol/vol of antibiotics (10 mg/mL.streptomycin 10000 U-1 mL penicillin), and incubated under standardconditions (95% RH and 5% CO2 at 37° C.). After 24 hours of incubation,the medium was removed and replaced with 200 μL of fresh mediumcontaining the empty micelles of INU-C8 and INU-C8-PEG at aconcentration equal to 0.025, 0.05, 0.1, 0.25, 0.5 and 1 mg/mL. After 4and 24 hours of incubation, the dispersion of micelles in DMEM wasremoved, the cells were washed 1 time with Dulbecco's Phospate bufferedsaline (DPBS) and incubated for 2 hours at 37° C. with 100 μL of freshmedium and 20 μL of MTS solution. The cells incubated with DMEM alonewere used as negative controls. The results were expressed as percentagereduction of the cell viability compared with control cells (FIGS. 4aand 4b ). All experiments were conducted in triplicate.

The studies conducted show that the polymeric micelles tested have agood cytocompatibility and do not exhibit cytotoxic effects in vitro onthe human bronchial epithelium cell line. This result makes thesesystems potentially usable as efficient systems for in vivo drugdelivery. The biocompatibility of the empty systems and loaded with theactive ingredients studied was also confirmed on ARPE-19 retinal cellsand on SIRC corneal epithelial cells.

The micellar carriers INU-C8 and INU-C8-PEG conjugated with silibinin orwith sorafenib tosylate were evaluated for the protective effect onretinal cells exposed to a pretreatment of 20 h and then insulted withH₂O₂ to induce an oxidative stress. The empty and conjugate INUC8PEGcarrier shows a protective action greater than the carrier without PEG,however only the carrier INUC8PEG conjugated with silibinin or withsorafenib is able to cause a decrease in the LDH release at higherconcentrations due to the presence of PEG. By way of example, FIG. 5Aand FIG. 6 show the experimental test data of the system conjugated withthe active ingredient sorafenib or silibinin, respectively.

In a post-treatment protocol, the retinal cells insulted for three hourswith H₂O, and subsequently exposed to treatment with the INU-C8 andINU-C8-PEG systems conjugated with silibinin or sorafenib show a goodability of both carriers to revert the insult-induced damage. However,the INUC8PEG system conjugated with either active ingredient is moreeffective in inhibiting the H₂O₂-induced stress. By way of example, FIG.5B and FIG. 6B show the experimental test data of the system conjugatedwith the active ingredient sorafenib or silibinin, respectively.

Lysates of retinal cells exposed to post-treatment with the INUC8PEGsyste, empty or conjugated with silibinin, were analyzed by westernblotting for the expression of the PARP-1 protein, a poly (ADP-ribose)polymerase of 116 kDa involved in DNA repair in response toenvironmental stress (Calcium Overload Is A Critical Step In ProgrammedNecrosis Of Arpe-19 Cells Induced By High-Concentration H ₂ O ₂ Guang-YuLi et al., (2010) Biomedical And Environmental Sciences). In vivo and invitro, PARP-1 is processed by Caspase 3 and Caspase 7 with the formationof a 24 kDa DNA-binding domain and an 89 kDa catalytic domain thatparticipates in the apoptosis (Importance of Poly (ADP-ribose)Polymerase and Its Cleavage in Apoptosis F. J Oliver et al., (1998) J.Biol. Chem.). FIG. 7 shows a reduction in the PARP-1 protein followingtreatment with H₂O₂ which confirms the cell apoptotic status.Conversely, in the samples treated with the conjugated carrier, higherexpression of PARP-1 is observed compared to the free carrier and Slbitself. The ability of INUC8PEG conjugated with Slb to inhibit theapoptosis induced by the oxidative damage is confirmed in adose-dependent manner in the samples treated with H₂O₂. Thepost-treatment with free Slb reduces the apoptotic process, however withless efficiency than the conjugated carrier.

Example 4 Preparation of Calixarene Nanoparticles

As an example, the procedure and the experimental data obtained with thecalix[4]arene derivative (compound 1)—loaded with silibinin, curcumin orlatanoprost is described hereinafter.

Preparation

The amphiphilic calix[4] arene derivative bearing four dodecyl aliphaticchains at the lower edge of the macrocycle and four polar heads ofcholine at the upper edge (compound 1) was synthesized, with good yield,adapting a procedure described in literature for similar derivatives.The compound was characterized by NMR spectroscopy and massspectrometry.

The assembly of the calixarene derivative in nanoaggregates occursspontaneously. The simple dissolution in PBS (pH 7.4) provides acolloidal solution containing nanoaggregates with size, polydispersityindex and zeta potential shown in table 6.

The drug loading was carried out by adding an excess of drug (molarratio 1:5) to the colloidal solution as bottom body. The mixture wasexposed to ultrasounds for 15 minutes and stirred in a shaker at 25° C.,200 rpm, for 2-3 days. The subsequent centrifugation at 4000 rpm for 30minutes and filtration on GHP Acrodisc 0.2 μm filter provides acolloidal solution of nanoparticles loaded with silibinin. Thefreeze-drying of this solution, without the addition of cryoprotectantsand using a standard freeze-dryer, provides a white powder thatresuspended in water restores the colloidal solution of nanoparticlesloaded with drug. The re-filtration of the colloidal solution on GHPAcrodisc 0.2 μm filter and subsequent HPLC analysis to determine the %DL show that following freeze-drying, the system retain the incorporateddrug load (table 6).

Size Determination and Zeta Potential Measurement

The average diameter, polydispersity index (PDI) and zeta potential ofcalixarene nanoparticles loaded and not with silibinin were measuredusing a Zetasizer Nano ZS-90 (Malvern Instrument), the reading was madeat an angle of 90° with respect to the incident ray and analyzed intriplicate. The results obtained for average diameter, PDI and zetapotential are given in Table 6.

TABLE 6 Average hydrodynamic diameter, polydispersity index (PDI), zetapotential of the calixarene nanoaggregates. DLS (in PBS, pH 7.4)Z-average Potential ζ (nm) PDI (mV ± SD) Calixarene nanoparticle (NP)44.3 0.29 24 Calixarene-silibinin nanoparticle 77.8 0.3 23.4NP-silibinin POST-freeze-drying 81.5 0.35 23

Determination of Drug Loading (% DL) of the Calixarene Nanoparticle

To determine the amount of silibinin loaded into a colloidal solutioncontaining 1 mg/mL of calixarene nanoparticle, an aliquot of thesolution was diluted with methanol and analyzed by HPLC. The amount ofdrug was measured considering the absorption band of silibinin at 288nm. The amount of drug was also measured at the UV spectrometerconsidering the 327 nm band of silibinin in PBS.

The results obtained in terms of % DL (expressed as a percentage ratiobetween weight of the active ingredient loaded and weight of the activeingredient loaded+weight of the nanoparticle) was found to be equal to10-11%.

Release in of Silibinin from the Calixarene NP in PBS at pH 7.4

The release of silibinin in phosphate buffer at pH 7.4 was investigatedin vitro at 37° C. with incubation times in the range between 0 and 12hours by dialysis. The results obtained have shown that the systemslowly releases the drug up to a maximum of 6.5% w/w within 12 hours(FIG. 7). The slow release might be advantageous for the purpose of drugdelivery in the pathological site.

Stability Study of the Calixarene Nanoparticle Loaded with Silibinin inPBS at pH 7.4

The stability of calixarene nanoparticles loaded with silibinin wasassessed by keeping the colloidal solutions in PBS at 25° C. Controls at7 and 14 days from the preparation show size, PDI and % DL valuesvirtually unchanged (table 10). The stability of the formulation is animportant pharmacological (e.g. achievement of the pathological sites atthe back of the eye) and industrialization requirement.

TABLE 10 Stability of the colloidal solution of calixarenenanoparticle-silibinin after 7 and 14 days at 25° C. Average diameterIncubation time (nm) PDI Time 0 77.8 0.3 7 dd 78.8 0.3 14 dd  80.6 0.3

Following preliminary investigations of the calixarene-choline carrierconjugated with silibinin in ARPE-19 cells, it was determined thatconcentrations of the carrier, either free or conjugated with Slbincluded in range 0.01-1 μM and incubated for 20 hours caused notoxicity. Then, the effects of the conjugated and empty system weretested using the compound FeSO₄ as oxidative insult, with changes in thecellular redox status. Over 24 hours of incubation, the cells arepre-treated for 20 h and then exposed to insult with 50 μM FeSO₄ forthree hours [“Pretreatment” 20 h drug+3 h insult]. The viability testconducted to evaluate the toxicity and the ability of protection fromdamage of the carrier in question is to assess the release of LDH in theculture medium. FIG. 8A shows a dose curve of the carrier conjugatedwith Slb (CalixSlb), of the empty carrier (Calix) and of silibinin alone(Slb) in ARPE cells subjected or not to insult with 50 μM FeSO₄. It isnoted that Slb reduces the release of LDH, while Calix Slb and the emptydo Calix do not significantly change the release of LDH of ARPE-19cells. Conversely, when the cells are exposed to FeSO₄ (50 μM), CalixSlb shows good potential in reducing the release of LDH, an effect notobserved in the samples treated with Calix and Slb individually. Theseresults suggest that calix and Slb may together prepare the cellstowards a protection against changes in the redox status.

In subsequent experiments, the effects of post-treatment with calixarenebased compounds were tested. Therefore, cells were treated with 50 μMFeSO₄ for 5 hours and incubated for 20 hours with the various compounds.As shown in FIG. 8B, CalixSlb protects against insult even inpost-treatment conditions and the effect is confirmed as a synergicaction of the two compounds that are individually able to protect fromthe redox status alteration.

FIG. 9A shows the western blot analysis of VEGF which shows a reductionin the expression levels of soluble VEGF after insult with FeSO₄, thisreduction is annulled by the empty Calix, by Slb and by Calix Slb at theconcentration 1 μM of Calix Slb. In fact, Calix Slb itself is able toincrease the levels of VEGF. These results are in agreement with theobservations reported by Lin et al. (Silibinin inhibits VEGF secretionand age-related macular degeneration in a hypoxia-dependent mannerthrough the PI-3 kinase/Akt/mTOR pathway C H Lin et al., (2013) BritishJournal of Pharmacology) on the inhibition of VEGF secretion underhypoxic conditions of ARPRE cells and pretreatment with the drug. Thelack of secretion leads to the lack of free VEGF that cannot act as aself-regulator of (autocrine signalling) with concomitant decrease ofthe angiogenic process.

Cathepsin D is an intracellular aspartyl protease, synthesized in theendoplasmic reticulum as pre-pro-enzyme that is processed up to generateactive fragments.

According to the cellular environment in which it resides, it can induceor inhibit apoptosis through different mechanisms. The 48 kDa fragmentis an active intermediate form from which two additional activefragments are generated; therefore, its reduction is associated with theactivation of the proteolytic process, vice versa its increase isindicative of an inhibition of apoptosis. In the presence of oxidativestress, the activation of cathepsin D may activate caspase 8 which inturn activates caspase 3, leading to cell death (Regulatory role ofcathepsin D in apoptosis, A. Minarowska et al., (2007) FoliaHistochemica et Cytobiologica) (Caspase-8-mediated apoptosis induced byoxidative stress is independent of the intrinsic pathway and dependenton cathepsins H. K. Baumgartner et al., (2007) Am J Physiol GastrointestLiver Physiol.). As shown in FIG. 9B, the exposure of cells to FeSO₄results in a reduction of the 48 kDa band of cathepsin D. Thepost-treatment with Calix or Slb increases the expression levels ofcathepsin D, but the greater increase in the protein is observed insamples treated with Calix Slb, confirming the potentiating effect ofthe conjugate in terms of protective activity, which is detected asinhibition of the apoptotic process in which cathepsin D is involved.

The calixarene carrier compound (1) lends itself to load a variety ofhydrophobic molecules, in this invention as an example, it was loadedwith curcumin and latanoprost in addition to silibinin. The above activeingredients are characterized by low water solubility, easy chemical andenzymatic degradation, low bioavailability. Curcumin and silibinin arenatural substances that are used in a variety of conditions ranging frominflammation to cancer, latanoprost is a prostaglandin F2α analog usedin the treatment of glaucoma, a condition that is still a leading causeof irreversible blindness in the world.

Also for these active ingredients, the loading of the active ingredientin the nanoaggregate compound (1) occurs through the phase solubilitymethod with drug loading ≧10%. The dosage of the active ingredient wasperformed by HPLC analysis and UV spectroscopy.

The nanoaggregate (compound 1) loaded with active ingredient wascharacterized by DLS and zeta potential measurements that showed thatnano-dimensions, polydispersity index and surface loading are stillsuitable for drug delivery systems (table 11)

TABLE 11 Chemical and physico-chemical features of aggregate 1 loadedwith active ingredient curcumin or latanoprost Chemical-physicalCarrier- requirements Carrier-Curcumin Latanoprost Dimensions ≦ 100 nm Zaverage 82 nm, Z = 65.7 nm D_(H) 113 nm Polydispersity ≦ 0.5 0.2 pdi =0.26 Zeta potential ≠ 0 23 mV Stability in PBS at DLS stable, [drug],DLS stable, [drug], room temperature LC over 15 days LC after 4 monthsSterilizability Filtration 0.2 μm Filtration 0.2 μm Drug loading % 10%45% Drug release % 20-30% EtOH/PBS dialysis 1-27% 24h

Calixarene 1 increases the solubility of curcumin as well as ofsilibinin in aqueous medium by at least ten times.

Calixarene 1 protects curcumin in PBS as a solvent, which shows adegradation of 80-90% in 30 min with 0.1 M PBS and in serum-free medium.(FIG. 10)

Calixarene 1 protects latanoprost from degradation (table 12) in PBS asa solvent at room temperature for over 6 months. This is an interestingresult because it allows the production of an innovative formulationwhich unlike those currently on the market, is released from the coldchain and is free from preservatives.

TABLE 12 Stability of the colloidal calixarene-latanoprost solution upto 4 months from preparation in PBS at room temperature: size, pdi,latanoprost concentration Z average pdi [drug] giorni t.a. 4° C. t.a. 4°C. t.a. 4° C. 0 69.2 69.2 0.26 0.26 52 54 6 72.0 72.3 0.30 0.29 54 56 1469.0 68.2 0.30 0.32 54 57 34 72.6 69.6 0.34 0.33 55 56 48 66.9 66.3 0.350.31 52 54 92 76.8 78.0 0.39 0.37 53 58 130 65.3 68.9 0.31 0.29 50 53

The colloidal solutions of calixarene 1, calixarene loaded with activeingredient and active ingredient alone were tested for cytotoxicity:SIRC corneal cells (FIG. 11), J774 macrophages (FIG. 12) and ARPEretinal cells. The results showed good biocompatibility of calixareneand of the calixarene-active ingredient combination on all cell typestested.

The anti-inflammatory activity of the colloidal solutions of calixarene1, calixarene-curcumin and curcumin alone was tested in vitro on j774cells subjected to inflammatory stress by insult with LPS. Inparticular, J774 cells were stimulated with lipopolysaccharide (LPS) ata concentration of 10 μg/mL for 24 hours, stimulation with LPS inducesthe activation of inflammatory processes such as NFκB nucleartranslocation and cytokine production, if not also release of nitritesand nitrosative stress. The cell viability was then evaluated followingstimulation with LPS (10 μg/mL for 24 hours) and 2-hour pretreatment ofthe delivery systems being studied at the different concentrations. Thecell viability following stimulation with LPS was reduced by 50%,treatment with the substances being examined such as curcumin, carrierand carrier associated with curcumin were able to restore the cellviability, almost returning it to the control levels, except for thehigher concentrations that already appeared to be toxic to insultedcells (FIG. 13). The anti-inflammatory activity of the delivery systemswas then evaluated through the Western Blot analysis. First, thedegradation of IκBα (FIG. 14) and the consequent NFκB translocation tothe nucleus (FIG. 15) were observed, which leads to the production andactivation of pro-inflammatory genes such as those encoding cytokines.The results show that the stimulation with LPS (10 μg/mL for 30 min)significantly increases the degradation of IκBα and the subsequenttranslocation of NFκB to the nucleus (whose levels are significantlyincreased, as can be seen in FIG. 15). On the contrary, thepre-treatment with the delivery systems is able to significantly reducethe degradation of IκBα and NFκB translocation (FIG. 15). The NFκBactivation involves the production of proteins and inflammatorymediators such as cyclooxygenase 2 (COX-2) and inducible nitric oxidesynthase (iNOS) and consequent increase in the production of nitrites.Through the Western blot analysis, it was observed that the stimulationwith LPS (10 μg/mL for 24 hours) significantly increases both the levelof iNOS and of COX-2. Pre-treatment with curcumin, carrier and carrierassociated with curcumin reduces significantly and in a dose-dependentmanner the levels of iNOS and COX-2 (FIG. 16)

The calixarene derivative not only carries out its activity as a carrierbut also has anti-inflammatory activity on the macrophages subjected toinflammatory stress with LPS.

The tests conducted showed an anti-inflammatory activity of calixareneloaded with curcumin>>calixarene>>curcumin

With the aim of verifying the effectiveness of the calixarene systemloaded with the active ingredient to the eye site of interest, anexperiment was conducted in vivo with an Uveitis model. Uveitis wasinduced in 160-180 g Lewis rats by single subcutaneous injection in thehind paw of 200 ig of the LPS endotoxin from Salmonella Minnesotadiluted in 0.2 mL PBS, pH 7.4. The control group received only 0.2 mL ofPBS in the hind paw. The rats were divided into treatment groups(calixarene system, calixarene-silibinin, silibinin alone,calixarene-curcumin and curcumin alone); pre-treated by topicaladministration for three days before the induction of uveitis, and laterto the point of sacrifice, which occurred for some animals at 16 andothers at 72 hours after the injection of the endotoxin. The eyes wereenucleated for histological and immunohistochemical analysis. Theaqueous humor was also taken for protein dosing.

The histological analysis of the eye tissues from animals injected withLPS showed signs of severe uveitis with a strong infiltration ofneutrophils. In animals treated with carrier alone, the degree ofinflammation was not reduced. Treatment with silibinin showed adecreased but not significant ocular inflammation while the associationof the calixarene+silibinin system reduced the damage.

However, treatment with curcumin and in particular with thecalixarene+curcumin combination significantly decreased the histologicdamage. No ocular inflammation was observed in the sham group.

Moreover, no significant difference was observed between the groups at16 h and 72 h. By way of example, the graph that summarizes thehistological score recorded for the various groups at time 72 h is shown(FIG. 17A). At 16 and 72 hours after injection of LPS, increased levelsof protein were observed in the aqueous humor of animals injected withLPS. Treatment with the carrier alone did not result in a reduction inthe protein levels in the eye tissue. Silibinin-treated animals showed atrend but not significant, while the calixarene+silibinin systemcombination significantly reduced the level of proteins in the aqueoushumor. However, curcumin and the calixarene+silibinin system combinationmost effectively determined the reduction of proteins in the oculartissue. The samples taken at 16 h and at 72 h showed a similar trend inall experimental groups, by way of example, the graph with the proteindosage found at time 72 h for the various treatment groups is shown(FIG. 17B).

In order to verify the effectiveness of the calixarene system loadedwith latanoprost, an in vivo experiment was set up with an ocularhypertension model induced in Brown Norway rats by episcleral veincauterization (EVC).

The treatments were carried out once a day by instilling 12 μL/eye (lefteye); the executive protocol involved a single administration treatmentfor the time course of the carrier system with the active ingredient,during which measurements of the intra ocular pressure (IOP) were takenafter 1 h, 3 h, 5 h, 7 h, 24 h, 30 h and 48 h; and a chronicadministration for seven consecutive days during which the measurementof IOP was evaluated every 24 h before the next instillation.

For each treatment group were made, each of which consisting of tenanimals; the average IOP measurements recorded at the different timepoints were compared with the average value of the baseline, previouslycalculated. The graphs (FIG. 18 NB) show the trend of loweringintraocular pressure (IOP) upon treatment with Calix+latanoprostcompared to the commercial product (IOPIZE) both alter singleadministration following the time course at different time points (FIG.18 A), and following chronic treatment for seven days (FIG. 18 B).

The trend of pressure variation for the two treatments is quite similar,both in the case of the calixarene-latanoprost system and in the case ofthe product IOPIZE, a paradox effect of latanoprost is observed duringthe first hours immediately following the administration and consistingof a marked increase in the IOP, this effect known in literature istypical in rats (Latanoprost-induced changes in rat intraocularpressure: direct or indirect? Husain S et al. J Ocul Pharmacal Ther.(2008); Effects of latanoprost on rodent intraocular pressure. Husain Set al. Exp Eye Res. (2006)), then a gradual lowering of pressure occurswhich reaches its peak only after 24 h to then tend to increase. Chronictreatment with the administration every 24 h allowed a lowering of IOPwhich reaches its highest point of bending around the fourth day withthe calixarene-latanoprost system. The calixarene system compared tocommercial products offers the advantage of releasing the product fromthe cold chain, of formulating the product without preservatives whilemaintaining the effectiveness of the active ingredient.

1-8. (canceled)
 9. Formulations containing an active ingredient selectedfrom: silibinin or sorafenib or curcumin or latanoprost wherein saidactive ingredient is incorporated in: (1) lipid nanoparticle systems ofthe SLN, Solid Lipid Nanoparticles, and NLC, Nanostructured LipidCarriers, type; (2) calixarene-based nanostructured systems; (3)micellar and nanoparticle systems based on amphiphilic inulincopolymers; possibly in the presence of mucoadhesives, for use in thetopical treatment of ocular diseases,
 10. Formulations according toclaim 9, wherein said ocular diseases are neurodegenerative oculardiseases.
 11. Formulations according to claim 9, wherein said lipidnanoparticle systems consist of lipids selected from: triglycerides,diglycerides, monoglycerides, aliphatic alcohols, fatty acids (C10-C22);fatty acid esters with fatty alcohols, mixtures of mono-, di- andtriglycerides of pegylated behenic acid, mono-, di- and triglycerides ofpegylated captylic and caproic acids.
 12. Formulations according toclaim 9, wherein said mucoadhesives are selected from: inulin polymersbearing amino groups, low molecular weight polymers and cationicsurfactants.
 13. Formulations according to claim 9, wherein saidnanoparticle systems have an average diameter in the range between 50and 200 nm with a polydispersity index below 0.5.
 14. Formulationsaccording to claim 11, wherein said systems incorporate an amount ofactive ingredient selected from: silibinin, sorafenib, curcumin,latanoprost in the range between 1 and 15% w/w.
 15. Formulationsaccording to claim 9, wherein said neurodegenerative ocular diseases areselected from: choroidal neovascularization (CNV), age-related maculardegeneration (AMD), macular edema, neovascular glaucoma, macular edema,retinopathy of prematurity (ROP), diabetic retinopathy (DR), uveitis,endophthalmitis, retinitis, choroiditis, chorioretinitis, retinalcomplications of systemic diseases.
 16. Compound of formula (A):

wherein: R═CH3, (CH₂)_(x)CH₃, (CH₂)_(x)OH R₁═CH3, (CH₂)_(x)CH₃,(CH₂)_(x)OH wherein x=1-3 n=4, 6, 8 m=2-15 and wherein when R═R₁═CH₃ mis different from 2-9.